CN106780329A - A kind of plane of ultrasound wave imaging method based on the conversion of anti-perspective plane - Google Patents
A kind of plane of ultrasound wave imaging method based on the conversion of anti-perspective plane Download PDFInfo
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Abstract
The invention discloses a kind of plane of ultrasound wave imaging method based on the conversion of anti-perspective plane, comprise the following steps：(1) gathered data；(2) data prediction：Using plane transformation, the imaging point on former imaging plane is first transformed to the imaging point in new plane, and time delay is carried out according to the imaging point in new plane be calculated revised time delay, then collectiong focusing is carried out to the imaging point on former imaging plane using synthetic aperture focusing technology further according to revised time delay, obtains the value of each imaging point on former imaging plane；(3) Data Post：Envelope detected, log-compressed and grey scale mapping are carried out successively, finally give plane of ultrasound ripple image.The present invention is improved by the calculation to crucial time delay, and is engaged with synthetic aperture focusing technology, and plane wave image quality problem not high is can effectively solve the problem that compared with prior art, effectively improves the imaging resolution of plane of ultrasound ripple.
Description
Technical field
The invention belongs to high-resolution ultrasound technical field of imaging, become based on anti-perspective plane more particularly, to a kind of
The plane of ultrasound wave imaging method for changing.
Background technology
Ultrasound detection has the advantages that directive property is good, cheap, harmless, equipment is easy to carry, therefore, with super
Sound wave carrys out irradiation object as the detection technique substitution ray of emission source, and the researchers for being increasingly becoming applications of ultrasound field chase after
One of fresh target asked.
Plane wave imaging only needs to once launch can just complete the imaging of whole area-of-interest, therefore be a kind of quick super
The ideal style of acoustic imaging, but compared with the multiple transmitting focusing of traditional ultrasonic imaging, plane wave is due in its emission process
Lack focusing so that only the picture quality resolution ratio that obtains is low, poor contrast by receiving to focus on.
At present, the method that plane wave image quality is improved both at home and abroad has a lot, such as changes the deviation angle of plane wave, emerging to feeling
The region Multiple-Scan of interest, then echo data is averagely rebuild.Also by Fourier transform, the sky of array signal is obtained
Between frequency spectrum, rebuild using the self adaptive imaging method of broad sense coherence factor.These methods are favorably improved the resolution of image
Rate and contrast, but also have respective advantage and disadvantage, reduce image taking speed on the basis of image quality raising.
The content of the invention
It is flat based on anti-perspective it is an object of the invention to provide one kind for the disadvantages described above or Improvement requirement of prior art
The plane of ultrasound wave imaging method of face conversion, wherein be improved by the calculation to crucial time delay, and with conjunction
It is engaged into aperture focusing technology, plane wave image quality problem not high is can effectively solve the problem that compared with prior art, effectively
The imaging resolution of plane of ultrasound ripple is improved, and the method processing speed is fast, it is only necessary to a transmitting for plane of ultrasound ripple, utilize
Many array elements are acquired to echo data.
To achieve the above object, it is proposed, according to the invention, there is provided it is a kind of based on anti-perspective plane conversion plane of ultrasound ripple into
Image space method, it is characterised in that comprise the following steps：
(1) gathered data：
Transmitting plane of ultrasound ripple, receives and gathers the data of ultrasonic reflection using array element, obtains raw radar data；
(2) data prediction：
Plane where note imaging plane is X-Z plane；
Then plane conversion is carried out, all of imaging point on primary plane (x, y, z) is all transformed into new plane by formula (1)
In (u, v, w), corresponding each imaging point in new plane is obtained,
Wherein, ai.jIt is conversion parameter set in advance, i=1,2,3, j=1,2,3；a33It is not zero；[dx dy dz] is
Coordinate translation vector between primary plane set in advance and new plane the two plane origins；
Then, for any one of array element, the collectiong focusing time delay of each imaging point in the new plane is calculated,
The collectiong focusing time delay is corresponded with each imaging point on the primary plane；Then, connect according to being calculated
Pinching Jiao's time delay, the raw radar data received to array element each described carries out synthetic aperture focusing imaging, so as to obtain
Take the component of each imaging point on the primary plane corresponding with each array element；
(3) Data Post：
Component to each imaging point on the primary plane is weighted averagely, each on the primary plane so as to obtain
The value of individual imaging point；Then envelope detected, log-compressed and grey scale mapping are carried out successively again, the imaging of plane of ultrasound ripple is finally given
Image.
Used as present invention further optimization, in the step (2), the plane conversion is to be based on anti-Perspective Principles, and
And, the plane conversion is only for the X-Z plane；
Preferably, the formula (1) is specially
Wherein, a33Correspond to nonlinear transformation coefficient.
Used as present invention further optimization, in the step (2), the formula (1) meets：
W=z+zexp (z/c)/n；
Preferably, c=1540, n=3.
As present invention further optimization, in the step (2), connecing for each imaging point in the new plane is calculated
Pinching Jiao's time delay, the collectiong focusing time delay is corresponded with each imaging point on the primary plane, specially：
The coordinate for remembering any one of array element i is (xi,zi), imaging point on any one of primary plane for P (x,
Z), then the collectiong focusing time delay
Wherein, R' the distance between is transducer center in the new plane to the corresponding imaging point in the new plane.
Used as present invention further optimization, in the step (3), the value I of each imaging point on the primary plane expires
Foot
Wherein, N is array element sum；In the raw radar data collected for corresponding array element withMoment corresponding echo data, i.e., on the primary plane corresponding with each array element that described step (2) obtains
The component of each imaging point；R is the distance between imaging point on the transducer center to the plane on the primary plane, and c is
The velocity of sound in soft tissue；Preferably, c=1540m/s.
As present invention further optimization, in the step (3),
The envelope detected, specifically for the value of each imaging point on the primary plane, detects its coenvelope, extracts
Go out low frequency component therein, as detected material information data；
The log-compressed, specifically takes the logarithm for the detected material information data for obtaining and is compressed, control compression
Data afterwards are between 40dB to 60dB；
The grey scale mapping, specifically for the data after the compression of acquisition, between using Linear Mapping for 0 to 255
Gray value, obtains gray value data.
By the contemplated above technical scheme of the present invention, compared with prior art, using plane transformation, first original is imaged
Imaging point in plane is transformed to the imaging point in new plane, and time delay is calculated according to the imaging point in new plane
Revised time delay is obtained, it is then flat to original imaging using synthetic aperture focusing technology further according to revised time delay
Imaging point on face carries out collectiong focusing, obtains the value of each imaging point on former imaging plane, is obtained in that with high-resolution
Plane of ultrasound ripple is imaged, and processing speed is fast, efficiency high.
The plane of ultrasound wave imaging method based on the conversion of anti-perspective plane that the present invention is provided, using conventional ultrasonic software
The plane wave data that (e.g., filedII) is produced, and for example, by SonixTouch DAQ system acquisitions detected materials (e.g., CIRS
Company 055A bodies film) reflected plane wave data, high resolution image reconstruction can be carried out；Simulation software (that is, filedII) and
SonixTouch DAQ systems can use linear array probe.When plane wave data carries out image reconstruction, it is assumed that ultrasound is situated between in ideal
Propagated in matter, less, the echo data according to generation is come image reconstruction for sonic velocity change.Use SAFT (Synthetic
Apertur Focusing Technique synthetic aperture focusings technology) method, using the echo-signal for receiving to each
Imaging point carries out collectiong focusing.Need first to carry out plane transformation before to each imaging point focusing, calculated in new plane and prolonged
The slow time, the value of imaging point after focusing on is calculated with new time delay, then result of calculation is mapped to primary plane.
Plane of ultrasound wave imaging method based on anti-Perspective Principles plane transformation proposed by the present invention, can further improve
The resolution ratio of image, improvement image quality, and do not increase the complexity of software and hardware, contribute to doctor clinically to examine disease
Disconnected and treatment.There is no the ultrasonic enterprise and research unit for grasping technique both at home and abroad at present, the technology does not have at home and abroad
People proposes.
Brief description of the drawings
Fig. 1 is calculating focusing time delay schematic diagram after plane conversion；
Fig. 2 is correspondence simulation result, and wherein Fig. 2A is to emulate data with fieldII to carry out traditional DAS (Delay and
Sum time delays are superimposed) rebuild, Fig. 2 B are comparison diagram after method proposed by the present invention rebuilds (that is, after plane transformation focus on)；
Fig. 3 is correspondence experimental result, and wherein Fig. 3 A are CIRS companies 055A body films, and Fig. 3 B, Fig. 3 C are respectively utilization
The plane wave data of SonixTouch DAQ system acquisitions carries out DAS reconstructions and method proposed by the present invention is rebuild and (that is, put down
Face conversion after focus on) after comparison diagram.
Specific embodiment
In order to make the purpose , technical scheme and advantage of the present invention be clearer, it is right below in conjunction with drawings and Examples
The present invention is further elaborated.It should be appreciated that the specific embodiments described herein are merely illustrative of the present invention, and
It is not used in the restriction present invention.As long as additionally, technical characteristic involved in invention described below each implementation method
Not constituting conflict each other can just be mutually combined.
The plane of ultrasound wave imaging method based on anti-Perspective Principles plane transformation is to collect ultrasonic system in the present invention
Initial data carry out appropriate treatment, finally rebuild ultrasonoscopy, its step include gathered data, data prediction, time delay
Superposition, weighted average, envelope detected, log-compressed, grey scale mapping, display.
Data acquisition is launched using plane wave, the mode of whole channel receptions, in order to obtain preferable plane wave image effect
Really, using the imaging of SAFT (that is, synthetic aperture focusing technique, synthetic aperture focusing technology)
Mode.Collectiong focusing is carried out to each imaging point using the echo-signal for receiving, plane transformation is first carried out, in new plane
Time delay between upper calculating passage (between i.e. each array element).
One plane conversion is that the process of another plane is called projection mapping.According to plane conversion formula
The upper all of point of primary plane (x, y, z) can be transformed into new plane (u, v, w), wherein ai.jFor conversion is joined
Number, [dx dy dz] is the coordinate translation vector between two plane origins.The present invention uses non-linear plane transformation
Mode, only carries out plane transformation to imaging plane X-Z, and other two planes keep constant.Plane transformation follows anti-Perspective Principles,
Using it is near it is small it is long-range by the way of, from origin more close to, convert it is smaller, from origin more away from, convert bigger, enter equivalent to X-Z plane
Stretching is gone, nearlyer stretching is smaller, more remote stretching is bigger.After each imaging point is mapped in new plane on primary plane, meter
The collectiong focusing time delay a little of correspondence institute is calculated in new plane, after obtaining whole time delays, further according to new time delay, is counted
Calculate each receiving channel on primary plane and in the influence of the imaging point, i.e., for each receiving channel, receive array element in the point
The echo data at place.
Hilbert transform (Hilbert-Huang Transform) will be carried out after all of echo data superposition at the point, finally
The point data value can be obtained.After the completion of each point in each imaging region is calculated, the matrix of M × N can be obtained
Data, M is the number of the imaging point set on each passage, and N is the element number of array of linear array, and data are carried out with log-compressed, ash
Degree mapping, the image rebuild.
Why image resolution ratio after reconstruction improves, because when being focused to imaging point, the focusing delay time
It is calculated in new plane, reduces the error of delay and focusing.Therefore, this plane wave imaging mode obtains tradition
Synthetic aperture imaging method be beyond one's reach high-resolution.
For example, may be selected to image plane for X-Z plane, plane transformation is only carried out on X-Z plane, before and after keeping converting
The origin of coordinates of two planes is constant, the founding mathematical models on X-Z plane, and the formula of plane conversion can be written as
a33It is non-linear transform coefficient, anti-Perspective Principles is applied to the amplification of X-Z plane, with the side of " near small long-range "
Formula is stretched to Z plane, and the coordinate relation of w and z can be designed to w=z+zexp (z/c)/n.C is the velocity of sound, and n is constant.
Selection c=1540, n=3.
After have passed through plane conversion, the imaging point (x, y, z) on primary plane is changed into (x, y, z+zexp in new plane
(z/c)/3), to each imaging point on primary plane, with computation delay on point of its one-to-one new plane.Such as Fig. 1 institutes
Show, for imaging point P (x, z), array element i (xi,zi) produced by delay focal time be
R arrives the distance between imaging point for transducer center, and c is the soft tissue velocity of sound.C=1540m/s.
By after plane transformation, imaging point P (x, z) on primary plane becomes the F (u, w) in new plane, it is believed that
There is a virtual imaging point in new plane, therefore generate a virtual focus point.According to formula (3), time delay is focused on
Formula can be rewritten as
Increased part zexp (z/c)/n changes with the change of imaging point position, and R' is in transducer in new plane
The heart calculates time delay of the every scan line for imaging point, by time delay the distance between to imaging point in new plane
For the calculating of original plane imaging point.The value of corresponding sampled point in corresponding scan line can be found by this time,
Corresponding value in all scan lines is added, the data of imaging point are can obtain, re-mapped on the corresponding position of original plane.Profit
The data of imaging point are can obtain with formula (5).I is the value of imaging point.A is the data of surface sweeping line, and N is port number.By to institute
There is imaging point to be calculated, finally give the matrix data for being used directly for reconstruction image.
The coenvelope of envelope detected detecting signal, extracts the low frequency component carried in echo-signal, i.e. testee letter
Breath.The method of the envelope detected used in the system is Hilbert transform method, and Hilbert transform is a kind of classical asking for
The method of signal envelope, primary signal will obtain the orthogonal signalling of primary signal by Hilbert transform, be with primary signal
Real part, complex signal is constructed with the signal that Hilbert transform is obtained as imaginary part, and the mould of this complex signal is exactly required real letter
Number envelope.
Primary signal is taken denary logarithm by log-compressed, and is multiplied by 20 multiple, and unit is dB.Take logarithm it
The dynamic range of echo can be adjusted afterwards, to obtain best real time imagery effect, 40dB or 60dB is generally adapted to, and its value is got over
Small contrast is higher.Specific method, is that the maximum in signal is mapped into 60dB by taking 60dB as an example, will be smaller than peak signal
The signal of 60dB and smaller signal are mapped to 0dB.
Grey scale mapping uses simple Linear Mapping, i.e., most weak signal proportionally is mapped into 0, by most strong signal
It is mapped to 255.
The display of image can be directly carried out by the data after grey scale mapping.Here the imaging in MATLAB is directly invoked
Function is that can obtain high-resolution ultrasound plane wave image.
Data Post process (e.g., envelope detected, log-compressed, grey scale mapping etc.) in the present invention also refers to existing
Technology is processed, as long as can finally obtain plane of ultrasound ripple image.
Certainly, except the plane conversion concrete mode employed in above-described embodiment and the calculating of corresponding time delay, imaging
Point value calculating outside, plane conversion can also other modes, both can be linear transformation, or other non-linear changes
Change, for example, the n in w=z+zexp (z/c)/n formula can also take other values (such as 2,4,5), as long as plane conversion is base
In anti-Perspective Principles, by the X-Z plane where former imaging surface by the way of " near small long-range " (that is, from origin more close to, conversion is got over
It is small；From origin more away from, convert it is bigger) to being stretched, origin position can keep constant before and after plane transformation.
As it will be easily appreciated by one skilled in the art that the foregoing is only presently preferred embodiments of the present invention, it is not used to
The limitation present invention, all any modification, equivalent and improvement made within the spirit and principles in the present invention etc., all should include
Within protection scope of the present invention.
Claims (6)
1. it is a kind of based on anti-perspective plane conversion plane of ultrasound wave imaging method, it is characterised in that comprise the following steps：
(1) gathered data：
Transmitting plane of ultrasound ripple, receives and gathers the data of ultrasonic reflection using array element, obtains raw radar data；
(2) data prediction：
Plane where note imaging plane is X-Z plane；
Then carry out plane conversion, by formula (1) by all of imaging point on primary plane (x, y, z) be all transformed into new plane (u,
V, w) in, corresponding each imaging point in new plane is obtained,
Wherein, ai.jIt is conversion parameter set in advance, i=1,2,3, j=1,2,3；a33It is not zero；[dx dy dz] is advance
Coordinate translation vector between the primary plane of setting and new plane the two plane origins；
Then, for any one of array element, the collectiong focusing time delay of each imaging point in the new plane is calculated, it is described
Collectiong focusing time delay is corresponded with each imaging point on the primary plane；Then, it is poly- according to the reception being calculated
Burnt time delay, the raw radar data received to array element each described carries out synthetic aperture focusing imaging, thus obtain with
The component of each imaging point on the corresponding primary plane of each array element；
(3) Data Post：
The component of each imaging point on the primary plane is weighted averagely, so as to obtain on the primary plane each into
The value of picture point；Then envelope detected, log-compressed and grey scale mapping are carried out successively again, plane of ultrasound ripple image is finally given
Picture.
2. the plane of ultrasound wave imaging method for being converted based on anti-perspective plane as claimed in claim 1, it is characterised in that the step
Suddenly in (2), the plane conversion is to be based on anti-Perspective Principles, also, the plane conversion is only for the X-Z plane；
Preferably, the formula (1) is specially
Wherein, a33Correspond to nonlinear transformation coefficient.
3. the plane of ultrasound wave imaging method for being converted based on anti-perspective plane as claimed in claim 1, it is characterised in that the step
Suddenly in (2), the formula (1) meets：
W=z+zexp (z/c)/n；
Preferably, c=1540, n=3.
4. the plane of ultrasound wave imaging method for being converted based on anti-perspective plane as claimed in claim 3, it is characterised in that the step
Suddenly in (2), the collectiong focusing time delay of each imaging point in the new plane, the collectiong focusing time delay and described Yuanping City are calculated
Each imaging point on face is corresponded, specially：
The coordinate for remembering any one of array element i is (xi,zi), the imaging point on any one of primary plane is P (x, z), then
The collectiong focusing time delay
Wherein, R' the distance between is transducer center in the new plane to the corresponding imaging point in the new plane.
5. the plane of ultrasound wave imaging method for being converted based on anti-perspective plane as claimed in claim 4, it is characterised in that the step
Suddenly in (3), the value I of each imaging point on the primary plane meets
Wherein, N is array element sum；In the raw radar data collected for corresponding array element withMoment corresponding echo data, i.e., on the primary plane corresponding with each array element that described step (2) obtains
The component of each imaging point；R is the distance between imaging point on the transducer center to the plane on the primary plane, and c is
The velocity of sound in soft tissue；Preferably, c=1540m/s.
6. the plane of ultrasound wave imaging method for being converted based on anti-perspective plane as claimed in claim 1, it is characterised in that the step
Suddenly in (3),
The envelope detected, specifically for the value of each imaging point on the primary plane, detects its coenvelope, extracts it
In low frequency component, as detected material information data；
The log-compressed, specifically takes the logarithm for the detected material information data for obtaining and is compressed, after control compression
Data are between 40dB to 60dB；
The grey scale mapping, specifically for the data after the compression of acquisition, the gray scale between using Linear Mapping for 0 to 255
Value, obtains gray value data.
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Cited By (6)
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| CN107845082A (en) * | 2017-12-14 | 2018-03-27 | 飞依诺科技(苏州)有限公司 | A kind of method and apparatus for being used to improve the contrast of regional area |
| CN110244305A (en) * | 2019-07-10 | 2019-09-17 | 南京信息工程大学 | A kind of emulation mode of Underwater Target Signal scattering |
| CN111580112A (en) * | 2020-06-11 | 2020-08-25 | 南京信息工程大学 | Underwater sonar sensor array imaging method based on plane waves |
| CN111965257A (en) * | 2020-08-07 | 2020-11-20 | 西南交通大学 | Space weighting optimized rapid ultrasonic plane wave imaging detection method |
| CN113436109A (en) * | 2021-07-08 | 2021-09-24 | 清华大学 | Ultrafast high-quality plane wave ultrasonic imaging method based on deep learning |
| CN117289276A (en) * | 2023-11-24 | 2023-12-26 | 航天宏图信息技术股份有限公司 | SAR image processing method and device, electronic equipment and storage medium |
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| 花少炎等: "基于压缩感知的超声衍射层析成像研究", 《生物医学工程学杂志》 * |
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